Fluorescence Imaging Flow Cytometry With Enhanced Image Resolution

ABSTRACT

In one aspect, a system for performing flow cytometry is disclosed, which comprises a laser for generating laser radiation for illuminating a sample, at least one detector for detecting at least a portion of a radiation emanating from the sample in response to said illumination so as to generate a temporal signal corresponding to said detected radiation, and an analysis module for receiving said temporal signal and performing a statistical analysis of said signal based on a forward model to reconstruct an image of said sample.

RELATED APPLICATION

The present application claims priority to provisional patent application No. 62/335,359 titled “Fluorescence Imaging Flow Cytometry With Enhanced Image Resolution” filed on May 12, 2016, and which is herein incorporated by reference its entirety. The present application is also related to utility patent application Ser. No. 15/461,124 titled “Cell Sorting Using A High Throughput Fluorescence Flow Cytometer,” filed Mar. 17, 2017, which is also herein incorporated by reference in its entirety.

BACKGROUND

The present invention relates generally to devices and methods for fluorescence analysis of samples, and more particularly to devices and methods for fluorescence-based flow cytometry.

Fluorescence imaging has a variety of biomedical applications, for example, in obtaining information regarding molecular composition of biological specimens. In biomedical flow cytometry, fluorescence radiation emitted by exogenous and/or endogenous cellular fluorophores is collected and analyzed to derive information about chemical and/or physical properties of cells.

In conventional fluorescence-based flow cytometry, however, the acquisition of blur-free images of cells flowing at a high speed, or other fast phenomena such as sub-millisecond biochemical dynamics, can be challenging. In particular, the weak optical emission of many fluorophores coupled with the short exposure of the sample at imaging frame rates in the kilohertz range renders the acquisition of blur-free images difficult. Moreover, many conventional systems operate in only one imaging mode and hence fail to provide sufficient flexibility for sample analysis.

Accordingly, there is a need for enhanced methods and systems for fluorescence analysis, and in particular a need for enhanced methods and systems for performing fluorescence-based flow cytometry.

SUMMARY

In one aspect, a system for performing flow cytometry is disclosed, which comprises a laser for generating laser radiation for illuminating a sample (e.g., a cell), at least one detector arranged to detect at least a portion of a radiation emanating from the sample in response to said illumination and to generate a temporal signal corresponding to said detected radiation, and an analysis module connected to the detector to receive said temporal signal and perform a statistical analysis of said signal based on a model, such as a forward model, to reconstruct an image of said sample. In some embodiments, the forward model is a linear model while in other embodiments, the forward model is a non-linear model.

In some embodiments, the radiation emanating from the sample can be a fluorescent radiation. The temporal signal is then a fluorescence signal on which the analysis module operates to form a fluorescence image of the sample.

In some embodiments, the radiation emanating from the sample can be a portion of laser radiation scattered by the sample and the analysis module can operate on the temporal signal corresponding to the scattered laser radiation to generate a darkfield image of the sample.

In some embodiments, the radiation emanating from the sample can be a portion of the illuminating laser radiation that is transmitted through the sample and the analysis module can operate on the temporal signal corresponding to the transmitted laser radiation to generate a brightfield image of the sample.

In some embodiments, the statistical analysis is based on generating maximum likelihood estimates of one or more parameters of said model. By way of example, the statistical analysis can employ a least squares method to reconstruct the image of the sample by minimizing a sum of squared residuals corresponding to a difference between the detected temporal signal and a respective temporal signal inferred from the forward model.

Some examples of statistical analyses suitable for use in the practice of the invention include, without limitation, least squares optimization, gradient descent optimization, particle swarm optimization, genetic algorithm optimization, and Bayesian spectral estimation.

In some embodiments, the analysis module forms an initial image of the sample and employs said image as an initial (seed) image for said statistical analysis. By way of example, the analysis module can employ any of Fourier transformation and lock-in detection for forming the initial image.

In some embodiments, the analysis module employs a model of the detected temporal signal as a plurality of temporal segments. By way of example, each temporal segment can be modeled as having a sinusoidal and a cosinusoidal term. In such embodiments, the statistical analysis can employ a least squares regression method so as to obtain values for parameters of the modeled temporal signal, e.g., amplitudes and phases of the sinusoidal and cosinusoidal terms, by minimizing a sum of squared residuals corresponding to differences between the modeled and corresponding measured temporal segments.

In some embodiments, the statistical analysis employs a gradient descent optimization method. In such embodiments, the gradient descent optimization method calculates an error gradient indicative of a distance between an expected temporal signal based on the forward model and the measured temporal signal and steps a previous estimate of an image of the sample down the error gradient to obtain an improved image. This process can be iteratively repeated until a best-fit image is obtained. The gradient descent optimization method can start the iterative process with an initial estimate of the image computed based on the measured temporal signal. By way of example, the analysis module can compute the estimate of the initial image via application of a Fourier transformation, e.g., FFT, to the measured temporal signal.

In some embodiments, the analysis module employs a priori information about the measured temporal signal in combination with Bayesian spectral estimation to reconstruct the image of the sample. By way of example, in some embodiments, such a priori information may indicate that the temporal signal is composed of a number of sinusoids of unknown frequencies, amplitudes, and phases. In addition, in some cases, the temporal signal may be known to include a noise component, e.g., a noise component having Poisson distribution. In such a case, the Bayesian spectral estimation can provide an estimate of the unknown frequencies, amplitudes and phases of the sinusoids as well as the parameters associated with the modeled noise.

In some embodiments, the laser radiation includes at least two optical frequencies shifted from one another by a radio frequency. By way of example, the radiofrequency shift can be in a range of about 10 MHz to about 250 MHz. In some such embodiments, the laser radiation can be in the form of a plurality of angularly separated laser beams each having a radio frequency shift relative to another. In some such embodiments, the temporal signal (e.g., a fluorescence signal) can be a time-frequency waveform exhibiting at least one beat frequency corresponding to a difference between said at least two optical frequencies.

In some embodiments, a sample under study can include any of a cell (e.g., a mammalian cell), a micro-vesicle, a cellular fragment, a liposome, a bead, or a small organism.

As discussed in more detail below, the analysis module can be implemented in hardware, firmware, and/or software. In some embodiments, such an analysis module can include, among other components, a processor that can communicate, via one or more communications buses, with one or more memory modules. The processor can execute a program implementing a forward model as well as statistical analysis according to the present teachings for reconstructing an image of a sample under interrogation in a flow cytometer.

In a related aspect, a method for performing flow cytometry is disclosed, which includes illuminating a sample (e.g., a cell) with a laser radiation, deploying a detector to detect at least a portion of a radiation emanating from the sample in response to said illumination and to generate a temporal signal corresponding to said detected radiation, and using a computer processor to perform a statistical analysis of the temporal signal based on a model, e.g., a forward model, so as to reconstruct an image of said sample. By way of example, the reconstructed image can be any of a fluorescence, a darkfield, and a brightfield image. In some embodiments, the laser radiation can include at least two optical frequencies that are shifted from one another by a radiofrequency, where the optical frequencies are selected to elicit fluorescence radiation from the sample. In such embodiments, the temporal signal can include one or more beat frequencies associated with the radiofrequency-shifted optical frequencies. Such a temporal signal can be processed to generate a seed fluorescence image on which the statistical analysis can be performed to reconstruct an enhanced image of the sample.

In some embodiments of the above method, the statistical analysis employs a least squares method to reconstruct the image of the sample by minimizing a sum of squared residuals corresponding to a difference between the detected temporal signal and a respective temporal signal inferred from the forward model. The temporal signal can be, for example, any of a fluorescence signal, a scattering signal, or a transmission signal.

In some embodiments, the temporal signal can be modeled as a plurality of temporal segments. In some such embodiments, each temporal segment can be modeled as having one sinusoidal and one cosinusoidal term. In such embodiments, the statistical analysis can employ a least squares regression method to obtain values for parameters of the modeled temporal signal by minimizing a sum of squared residuals corresponding to differences between the modeled and the respective measured temporal segments.

In some embodiments, the statistical analysis employs a gradient descent optimization method to reconstruct the image. The gradient descent optimization method can calculate an error gradient indicative of a distance between an expected temporal signal computed based on the forward model and the measured temporal signal and can iteratively compute an updated image by stepping a previous image down the error gradient. The iterative process can start with an initial estimated image of the sample computed based on the measured temporal signal, e.g., via application of a Fourier transformation to the measured temporal signal.

In some embodiments of the above method, the statistical analysis can employ a priori information about the measured temporal signal in combination with Bayesian spectral estimation to reconstruct the image of the sample. By way of example, in some embodiments, the a priori information can indicate that the temporal signal is composed of a plurality of sinusoids of unknown frequencies, amplitudes and phases. The Bayesian spectral estimation can provide estimates of the frequencies, amplitudes and phases. In addition, in some cases, the a priori information can indicate that the temporal signal can include a noise component having a Poisson frequency distribution. The Bayesian estimation can determine the parameters of the noise component.

In other embodiments of the above method, the statistical analysis can employ any of a particle swarm or a genetic optimization method.

The above method can be employed to obtain images of a variety of different samples, such as sample containing cells (e.g., mammalian cells), micro-vesicles, cellular fragments, liposomes, beads or small organisms.

Further understanding of various aspects of the invention can be obtained by reference to the following detailed description in conjunction with the associated drawings, which are described briefly below.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 schematically depicts a system in accordance with an embodiment of the invention,

FIG. 2A is a schematic, exemplary profile of a Gaussian beam in a plane perpendicular to the beam's propagation direction,

FIG. 2B is a schematic, top-hat beam profile obtained by passing the Gaussian beam shown in FIG. 2A through a top-hat beam shaper and focusing the output beam of the beam shaper,

FIG. 3 schematically depicts components of an exemplary top-hat beam shaper,

FIG. 4 schematically depicts cross-sectional beam profiles of a plurality of RF comb beams,

FIG. 5 schematically depicts superposition of the RF comb beams depicted in FIG. 4 and an LO beam having a top-hat beam profile,

FIG. 6 schematically depicts the combined beam shown in FIG. 5 illuminating a sample under analysis,

FIG. 7 schematically depicts exemplary energy levels of a hypothetical fluorophore,

FIG. 8 schematically depicts an absorption curve corresponding to the hypothetical fluorophore of FIG. 7,

FIG. 9A schematically depicts a detection system according to an embodiment of the present teachings, which includes an optical fiber for transmission of fluorescence radiation

FIG. 9B schematically depicts another detection system according to an embodiment of the present teachings in which fluorescence radiation propagates through free space to reach a plurality of photodetectors,

FIG. 9C schematically depicts a brightfield and a darkfield image generation arms for use in some embodiments of the present teachings,

FIG. 9D schematically depicts a detection system for use in some embodiments of the present teachings, which includes a detection arm for generating a brightfield image and a detection arm which integrates the capabilities for the detection of excitation radiation scattered from a sample as well as fluorescence radiation emitted by the sample,

FIG. 10 schematically depicts that a fluorescence signal generated by a photodetector in an embodiment of a system according to the present invention can be amplified by an amplifier and the amplified signal can be analyzed by an analysis module to construct a fluorescence image of a sample under analysis,

FIGS. 11A and 11B depict various steps in a method according to an embodiment of the present invention for analysis of fluorescence signal obtained by illuminating a sample with a combined beam composed of a plurality of RF comb beams and a top-hat profiled LO beam,

FIG. 12 schematically depicts selected components of an exemplary hardware implementation of an analysis module according to an embodiment of the present invention,

FIGS. 13A and 13B depict various steps in another method according to an embodiment of the invention for analysis of fluorescence signal obtained by illuminating a sample with a combined beam composed of a plurality of RF comb beams and a top-hat profiled LO beam,

FIGS. 14A and 14B depict various steps in yet another method according to an embodiment of the invention for analysis of fluorescence signal obtained by illuminating a sample with a combined beam composed of a plurality of RF comb beams and a top-hat profiled LO beam,

FIG. 15A schematically depicts illumination of a sample by a top-hat profiled beam at a single excitation frequency,

FIG. 15B is a schematic view of a system according an embodiment of the present teachings that allows for fluorescence lifetime measurements and fluorescence lifetime imaging,

FIG. 16A is a scatter plot of darkfield intensity versus brightfield intensity of polystyrene beads stained with 8 discrete level of fluorescence dyes obtained by using a cytometry system in accordance with an embodiment of the present teachings,

FIG. 16B shows a scatter plot of red fluorescence (PE) v. green fluorescence (FITC) emitted by a plurality of the polystyrene beads, where the data was obtained by using the rectangular section of the plot shown in FIG. 16A as a gate,

FIGS. 16C and 16D are histograms corresponding to the data shown in FIG. 16B,

FIG. 17A shows brightfield, darkfield and fluorescence images of a sample containing fixed peripheral blood leukocytes stained with anti-CD45-FITC, and propidium iodide obtained using a cytometry system according to the present teachings, where the sample also contained a fraction of live HeLa cells that were stained with Calcein-AM,

FIG. 17B is a scatter plot in which population A represents leukocytes and population B represents HeLa cells in the sample for which FIG. 17A provides images,

FIG. 18A shows brightfield, darkfield and fluorescence images of a sample containing fixed peripheral blood leukocytes stained with anti-CD45-FITC and propidium iodide obtained using a cytometry system according to an embodiment of the present teachings, where the sample was spiked with a small fraction of fixed MCF-7 cells stained with anti-EpCAM-FITC and propidium iodide,

FIG. 18B is a scatter plot in which population A represents leukocytes and population B represents MCF-7 cells in the sample for which FIG. 18A provide images,

FIG. 19A is a flow chart depicting various steps in an embodiment of a method according to the present teachings for performing flow cytometry in which statistical analysis is employed for reconstructing an image of a sample under interrogation,

FIG. 19B is a flow chart depicting various steps in an embodiment of a method according to the present teachings for performing flow cytometry in which a cytometry signal is modeled as a plurality of temporal segments and a least squares regression analysis is used to obtain estimated values for parameters of the model,

FIG. 19C is a flow chart depicting various steps in an embodiment of a method according to the present teachings for obtaining image of a sample from a cytometry signal obtained from the sample in response to illumination thereof,

FIG. 19D is a flow chart depicting various steps in an embodiment of a method according to the present teachings for performing flow cytometry in which a gradient descent optimization method is used to iterative improve an image estimate of a sample so as to obtain a best-fit image of the sample,

FIG. 20 schematically depicts modeling various components of a cytometric system according to an embodiment of the present teachings,

FIG. 21A depicts measurements of light extinction and scattering by an elongated Euglena cell,

FIG. 21B shows an image of the Euglena cell by extracting the Fourier components of the signal depicted in FIG. 21A,

FIG. 21C depicts an improved image of the Euglena cell by utilizing a model of excitation, and electronic and phase response of the system in accordance with an embodiment of the present teachings,

FIG. 22A depicts a FIRE (radio-frequency-tagged emission) measurement of the lipid content of the Euglena cell depicted in FIGS. 21B and 21C,

FIG. 22B an image obtained via extraction of the Fourier coefficients of the signal depicted in FIG. 22A,

FIG. 22C an improved version of the image shown in FIG. 22B obtained by incorporating information about the frequency response of the collection electronics, the underlying FIRE signal driving the system, and the phase response of the system, and

FIG. 22D an improved version of the image shown in FIG. 22B obtained by employing a model of the underlying signal, and the impact of the photonic shot noise.

DETAILED DESCRIPTION

The present teachings relate generally to methods and systems for performing flow cytometry, e.g., fluorescent analysis of samples. In some embodiments, statistical techniques can be employed in reconstruction of any of fluorescence, brightfield and darkfield images from temporal data, e.g., in the form of time-frequency waveforms, obtained from a sample in response to the illumination of the sample by interrogating radiation (e.g., laser radiation). The temporal data can be obtained using a variety of different systems. In some embodiments disclosed below, the temporal data can be generated by illuminating a sample with an optical beam having a plurality of radiofrequency-shifted beamlets. Examples of such embodiments are described below, but the teachings of the invention are not limited to these embodiments.

In many embodiments, the use of such statistical techniques can advantageously improve spatial resolution, intensity resolution, and/or signal-to-noise ratio of the reconstructed images. In some embodiments, an initial (seed) fluorescent, a brightfield or a darkfield image can be reconstructed using, e.g., FFT analysis of the signal. Subsequently, at least one of the statistical techniques discussed below can be applied to the image to generate an enhanced image. In some embodiments, the statistical techniques can be employed to fit parameters of a model directly to fluorescence, brightfield and/or darkfield signals detected by one or more detectors, e.g., in a manner discussed below.

Various terms used below to describe the present teachings have their ordinary meaning in the art, unless stated otherwise. For example, the term “fluorophore” is used herein consistent with its customary meaning in the art to refer to a fluorescent chemical compound that can emit radiation in response to illumination by excitation radiation.

The terms “cytometry” and “flow cytometry” are also used consistent with their customary meanings in the art. In particular, the term “cytometry” can refer to a technique for identifying and/or sorting or otherwise analyzing cells. The term “flow cytometry” can refer to a cytometric technique in which cells present in a fluid flow can be identified, and/or sorted, or otherwise analyzed, e.g., by labeling them with fluorescent markers and detecting the fluorescent markers via radiative excitation. The terms “about” and “substantially” as used herein denote a maximum variation of 10%, or 5%, with respect to a property including numerical values.

The term “forward model” refers to a mathematical model of a system or a process for mathematically predicting an output of the system or the process for a given input (e.g., one or more input parameters). By way of example, in some of the following embodiments, a forward model can be a mathematical model of a pixelated image of a sample under interrogation in a flow cytometer, which can be used to predict a temporal signal obtained from the sample in response to illumination thereof in the flow cytometer. A statistical analysis can then be used to refine the parameters of the model, e.g., by minimizing the difference between the predicted temporal signal and a measured temporal signal, e.g., a signal measured by detecting radiation emanating from the sample in response to illumination by interrogating radiation, such as an RF-modulated illuminating radiation.

FIG. 1 schematically depicts a system 10 for performing cytometry according to an embodiment of the present teachings, which can be operated in three operational modes. As discussed in more detail below, in one operational mode, a sample under study can be illuminated concurrently with a plurality of excitation frequencies, each of which can be obtained, e.g., by shifting the central frequency of a laser beam. More specifically, a plurality of sample locations can be concurrently illuminated by a laser beam that is generated by mixing a reference laser beam (herein also referred to as a local oscillator beam) with a plurality of radiofrequency-shifted laser beams such that each sample location is illuminated by the reference beam and one of the radiofrequency-shifted beams to excite a fluorophore of interest at that location, if present. In some embodiments, the reference beam can itself be generated via radiofrequency shifting of a laser beam. Thus, each spatial location of the sample can be “tagged” with a different beat frequency corresponding to a difference between the frequency of the reference beam and that of one of the radiofrequency-shifted beams. In other words, the fluorescence radiation emitted by the fluorophore will spatially encode the beat frequencies. The fluorescence emission can be detected and its frequency components can be analyzed to construct a fluorescence image of the sample.

In another operational mode, a sample can be illuminated successively over a time interval by a laser beam at a plurality of excitation frequencies. In some such embodiments, the excitation frequencies can be obtained by applying a time-varying drive signal to an acousto-optic deflector (AOD), which receives a laser beam. In many embodiments, the laser beam has a frequency in the hundreds of terahertz (THz) range, e.g., in a range of about 300 THz to about 1000 THz. The drive signal applied to the AOD is typically in the radiofrequency range, e.g., in a range of about 10 MHz to about 250 MHz. The passage of the laser beam through the AOD generates a plurality of diffracted beams, each corresponding to a different diffraction order. While the zero^(th) diffracted beam exhibits no frequency shift relative to the frequency of the input laser beam, the higher-order diffracted beams exhibit a frequency shift relative to the frequency of the input laser beam corresponding to the frequency of the drive signal or a multiple thereof. In some embodiments, the first order diffracted beam having a frequency corresponding to the frequency of the input laser beam shifted by the drive signal is employed as the excitation beam for exciting a fluorophore of interest, if present in a sample under analysis. As the drive signal varies over time, the frequency and angular shift of the first-order diffracted beam also varies, thereby allowing the illumination of the sample at different excitation frequencies at different locations. The fluorescence emission, if any, from each illuminated location can be collected and analyzed to construct a fluorescence image of the sample.

In yet another operational mode, the system 10 can be operated to illuminate a plurality of locations of a sample concurrently by a single excitation frequency, which can be generated, e.g., by shifting the central frequency of a laser beam by a radiofrequency. For example, a horizontal extent of the sample can be illuminated by a laser beam at a single excitation frequency. The detected fluorescence radiation can be used to analyze the fluorescence content of the sample, e.g., a cell/particle.

Thus, one advantage of system 10, among others discussed below, is that it provides significant flexibility in obtaining fluorescence emission data in different modes without a need to utilize different instruments or to make any mechanical modifications to the system when switching between different operational modes.

In certain embodiments, systems include one or more light sources. In some instances, the light source is a narrow band light source, including but not limited to a narrow wavelength LED, laser or a broadband light source coupled to one or more optical bandpass filters, diffraction gratings, monochromators or any combination thereof which in combination produces a narrow band of illuminating light. In certain instances, the light source is a single wavelength laser, such a single wavelength diode laser (e.g., a 488 nm laser). In some embodiments, the subject systems include a single light source (e.g., a laser). In other embodiments, the subject systems include two or more different light sources, such as 3 or more different light sources, such as 4 or more different light sources and including 5 or more different light sources. For examples, systems may include a first light source (e.g., a laser) outputting a first wavelength and a second light source outputting a second wavelength. In other embodiments, systems include a first light source outputting a first wavelength, a second light source outputting a second wavelength and a third light source outputting a third wavelength.

Each light source may have a wavelength which ranges from 300 nm to 1000 nm, such as from 350 nm to 950 nm, such as from 400 nm to 900 nm and including from 450 nm to 850 nm. In certain embodiments, the light source has a wavelength that corresponds to an absorption maximum of one or more fluorophores (as described below). For example, the light source may output light having a wavelength that is in the range of one or more of 280-310 nm, 305-325 nm, 320-350 nm, 370-425 nm, 400-450 nm, 440-500 nm, 475-550 nm, 525-625 nm, 625-675 nm, and 650-750 nm. In certain embodiments, each light source outputs light having a wavelength that is selected from 348 nm, 355 nm, 405 nm, 407 nm, 445 nm, 488 nm, 640 nm and 652 nm.

The system 10 includes a laser radiation source 12 generating a laser beam 14. By way of example, the laser beam can have a frequency in a range of about 1000 THz to about 300 THz, corresponding to a vacuum wavelength in a range of about 300 nm to about 1000 nm. The beam diameter of the laser beam (e.g., the beam waist when a Gaussian laser beam is employed) can be, for example, in a range of about 0.1 mm to about 10 mm. Without any loss of generality, in this embodiment the laser 12 emits radiation at a wavelength of 488 nm with a beam diameter of about 1 mm.

The frequency of the laser beam can be selected based on a particular application(s) for which the system is intended. Specifically, as discussed in more detail below, the laser frequency can be suitable for exciting an electronic transition of a fluorophore of interest, e.g., via absorption of the radiation, so as to cause the fluorophore to emit fluorescence radiation at a lower frequency. A variety of laser sources can be employed. Some examples of such laser sources include, without limitation, Sapphire 488-SF, marketed by Coherent, Inc. of Santa Clara, Calif. U.S.A., Genesis MX-488-1000-STM (Coherent, Inc.), OBIS 405-LX (Coherent, Inc.), Stadus 405-250 marketed by Vortran Laser Technology, Inc. of Sacramento, Calif. U.SA., and LQC-660-110 of Newport Corporation of Irvine, Calif. U.S.A. Without any loss of generality, in the present embodiment the laser beam is assumed to have a Gaussian intensity profile in a plane perpendicular to its propagation direction.

A mirror 16 receives the laser radiation beam 14 and directs the laser beam via reflection to an acousto-optic deflector (AOD) 18. In this embodiment, the AOD 18 is mounted on an adjustable post holder mount (A) that allows rotation of the AOD about an axis perpendicular the propagation direction of the beam 14. A direct digital synthesizer (DDS) 20 operating under control of a controller 21 can apply one or more drive signals to the AOD 18. By way of example, in some embodiments, these drive signals can span a frequency range of about 50 MHz to about 250 MHz. In some embodiments, the drive signals may be separated from one another by a frequency in a range of about 0.1 MHz to about 4 MHz. In this embodiment, an electronic power amplifier 21′ amplifies the radiofrequency signals generated by the DDS 20 for application to the AOD 18.

In the operational mode in which a sample is illuminated concurrently with a plurality of excitation frequencies, the RF comb generator 20 applies a plurality of RF drive signals concurrently to the AOD 18. By way of example, the number of simultaneously applied RF drive signals can be in a range of about 20 to about 200. The interaction of the laser beam and the drive signals results in generation of a plurality of angularly separated laser beams each having a frequency shift corresponding to one of the drive signals relative to the frequency of the laser beam generated by the laser 12. Without being limited to any particular theory, in an AOD, a piezoelectric transducer can generate radiofrequency phonons in a crystal, e.g., a quartz crystal, and the scattering of the optical photons of the laser beam by such radiofrequency phonons can result in the generation of the frequency-shifted laser beams. One of these frequency-shifted beams 22 is herein referred to as a “local oscillator” (LO) beam and the remainder of the frequency shifted beams 24 are herein referred to as “RF comb beams.” The angular separation of the frequency shifted beams can be, for example, in a range of about 1 milliradians to about 100 milliradians.

The LO and the RF comb beams pass through a lens 26, which is in this embodiment a positive lens with a focal length of about 50 mm. After passage through the lens 26, the LO laser beam is intercepted by a mirror 28, which redirects the LO beam in a different direction (in this embodiment in a direction substantially orthogonal to the original propagation direction of the LO beam). The mirror 28 is positioned relative to the RF comb beams such that these beams miss the mirror 28 and propagate to a lens 30 (which in this embodiment has a focal length of 200 mm). In this manner, the LO beam and the RF comb beams are directed along different propagation directions. The use of the pickoff mirror 28 in a manner disclosed above allows utilizing a single AOD to generate both the LO beam and the RF comb beams and combining them in a manner discussed below to generate an excitation beam for illuminating a sample. The use of a single AOD, rather than multiple AODs (e.g., two AODs, one for generating the LO beam and the other for generating the RF comb beams), simplifies the design of the system and further allows efficient use of the system in multiple distinct operational modes, as discussed in more detail below.

In some embodiments, the beam profile of the LO beam is modified before recombining with the RF beam combs. For example, the beam profile of the LO beam may be adjusted (increased or decreased) in spatial dimension, beam shape, intensity, spatial distribution of beam, or any combination thereof. In certain embodiments, the spatial dimensions of the beam profile of the LO beam are modified. For example, the beam profile may be adjusted to elongate the beam profile in one or more dimensions, such a long an axis that is orthogonal to the longitudinal axis of a flow stream. In one example according to these embodiments, the spatial dimension (e.g., in one or more dimensions) of the beam profile may be increased by 1% or more, such as by 2% or more, such as by 3% or more, such as by 5% or more, such as by 10% or more, such as by 25% or more, such as by 50% or more, such as by 75% or more, such as by 25% or more, such as by 50% or more, such as by 75% or more, such as by 90% or more, such as by 1.5-times or more, such as by 2-times or more, such as by 3-times or more and including 5-times or more. In another example according to these embodiments, the spatial dimension (e.g., in one or more dimensions) of the beam profile may be decreased by 1% or more, such as by 2% or more, such as by 3% or more, such as by 5% or more, such as by 10% or more, such as by 25% or more, such as by 50% or more, such as by 75% or more, such as by 90% or more, such as by 1.5-times or more, such as by 2-times or more, such as by 3-times or more and including by 5-times or more.

In other embodiments, the beam shape of the LO beam is modified. For example, the beam shape may be modified to elongate the beam profile in one or more dimensions. In certain instances, the beam shape of the LO beam is elongated in a plane perpendicular to the propagation of the LO beam. In certain embodiments, the shape of the LO beam profile is changed from a circular beam profile to an oval beam profile that is elongated in an axis orthogonal to the longitudinal axis of the flow stream. In other embodiments, the shape of the LO beam profile is changed from a circular beam profile to a rectangular beam profile that a long dimension in an axis orthogonal to the longitudinal axis of the flow stream. In still other embodiments, the intensity of the LO beam is modified. For example, the intensity of the LO beam may be increased, such as by 1% or more, such as by 2% or more, such as by 3% or more, such as by 5% or more, such as by 10% or more, such as by 25% or more, such as by 50% or more, such as by 75% or more, such as by 90% or more, such as by 1.5-times or more, such as by 2-times or more, such as by 3-times or more and including by 5-times or more. In certain embodiments, the intensity of the LO beam is modified to match the intensity of the RF comb beam. For example, the LO beam may have an intensity that differs from the intensity of the RF comb beams by 10% or less, such as by 9% or less, such as by 8% or less, such as by 3% or less, such as by 2% or less, such as by 1% or less, such as by 0.01% or less and including where the intensity of the LO beam differs from the RF comb beam by 0.001% or less. In certain instances, the intensities of the LO beam and the RF comb beams are identical.

In yet other embodiments, the spatial distribution of the beam profile may also be modified. For example, the LO beam may be modified such that the intensity of the LO beam is no longer Gaussian in one or more dimensions. For example, the LO beam may be modified to have a Gaussian distribution along a first axis that is parallel to the longitudinal axis of the flow stream and non-Gaussian along a second axis that is orthogonal to the longitudinal axis of the flow stream.

Any beam shaping protocol may be employed to modify the beam profile of the LO beam, including but not limited to refractive and diffractive beam shaping protocols. In some embodiments, the LO beam is modified by a top-hat beam shaper.

In this embodiment, the LO beam propagates to another positive lens 32 (which in this embodiment has a focal length of about 200 mm). The combination of the lens 26 and the lens 32 magnifies and collimates the LO beam in order to appropriately fill the back aperture of a top-hat beam shaper 34. More specifically, the LO beam 22 passes through the lens 32 and is reflected by mirrors 33 and 35 to the top-hat beam shaper 34.

The top-hat beam shaper 34 shapes the phase front of the Gaussian LO beam to enable formation of a top-hat intensity profile. More specifically, the LO laser beam 22′ exiting the top-hat beam shaper is reflected by a beam splitter 44 and is focused by lens 46 (which in this embodiment has a focal length of 100 mm) onto an intermediate image plane 48. The laser beam on the intermediate image plane 48 has a top-hat intensity profile along a horizontal direction in a plane perpendicular to the propagation direction of the beam. Similar to the AOD 18, in this embodiment, the beam splitter 44 is mounted on an adjustable post holder mount (B). In this embodiment, the top-hat beam shaper generates a top-hat beam profile in which the polarization of radiation is substantially uniform along the top-hat direction of the beam (along the horizontal direction in this embodiment).

By way of illustration, FIG. 2A schematically depicts the Gaussian intensity profile of the LO laser beam as it enters the top-hat beam shaper. As shown schematically in FIG. 2B, on the intermediate image plane 48, the LO laser beam exhibits a beam profile that is stretched in the horizontal direction (in a direction perpendicular to the page in this illustration) and is substantially constant along each horizontal line extending through the profile, e.g., the horizontal line A, but varies vertically according to a Gaussian profile.

A variety of top-hat beam shapers can be employed. By way of example, refractive optical elements having an aspherical surface or diffractive optical elements can be used to produce beams with appropriate spatial phase fronts, which, after focusing by a lens, will produce a top hat profile pattern at the focal plane of the lens. Multiple form factors exist for such top-hat beam shapers, and a variety of implementations of this approach are available to create the appropriate LO beam shape at the sample in various embodiments of the present teachings. For example, U.S. Pat. No. 6,295,168 entitled “Refractive optical system that converts a laser beam to a collimated flat-top beam” and U.S. Pat. No. 7,400,457 entitled “Rectangular flat-top beam shaper,” both of which are herein incorporated by reference in their entirety, disclose beam shaping systems that can be employed as the flat-top beam shaper in a system according to some embodiments of the present teachings. By way of illustration, FIG. 3 is a reproduction of FIG. 1 of U.S. Pat. No. 7,400,457 (with different reference numerals) that schematically depict a beam shaping system 300 for providing a square or a rectangular beam, which includes two orthogonally disposed acylindrical lenses 302 and 304. The first acylindrical lens 302 is for shaping an incident beam A along the X-axis and the second acylindrical lens 304 for shaping the incident beam A along the Y-axis. The two crossed acylindrical lenses are adapted to provide a resulting rectangular laser beam B having a flat-top profile along the X-axis. The input surface 302 a of the acylindrical lens 302 is a convex acylindrical surface having a variable radius of curvature that is smaller in the center of the surface and increases smoothly toward both X-extremities of the lens. The second acylindrical lens 304 is similar to the first acylindrical lens but is orthogonally disposed relative to the lens 302 in order to shape the beam along the Y-axis. The profiles of input surfaces 302 a/304 a, and output surfaces 302 b/304 b of the lenses 302 and 304 can be independently selected as a function of the X and Y-profiles of the incident beam A and the desired intensity profile of the resultant rectangular beam B (See, e.g., columns 5 and 6 of the patent).

An example of a commercially available top-hat beam shaper that can be employed include, for example, DTH-1D-0.46 deg-4 mm marketed by Osela, Inc. of Lachine, Canada.

As discussed in more detail below, the use of a beam shaper to stretch the LO beam along the horizontal direction provides a number of advantages. For example, it can ensure that the combination of the LO beam and the RF comb beams illuminates a plurality of sample locations with a substantially similar illumination intensity, in order to match the intensities of the LO and RF comb beams across the entirety of the sample locations, thereby creating an intensity amplitude modulation of the fluorescence signal with high modulation depth. In absence of such intensity matching, the imaging system may have a small view and may not utilize all of the frequencies (pixels) driving the AOD. As the modulation depth of the fluorescence signal plays an important role in the ability of the system to reconstruct a fluorescence image of the sample, a uniformly-high modulation depth of the excitation beat frequencies at all pixels is particularly advantageous to the operation of the system. Further, the amplitudes of electronic signals applied to the AOD for generating the RF comb beams can be adjusted by controlling the output of the direct digital synthesizer (e.g., by employing the controller 21) in order to equalize the RF comb beams such that their intensities are equal to that of the LO beam across all spatial locations in which the RF comb beams and the LO beam overlap. This feature provides an advantage in that it ensures high modulation depth of the intensity amplitude modulation of the fluorescence radiation.

Referring again to FIG. 1, the RF comb beams 24 are imaged via the combination of the lenses 26 and 30 onto an intermediate image plane 38. More specifically, the RF comb beams 24 pass through the lens 26 and miss the mirror 28 to reach the lens 30, which directs the RF comb beams via mirrors 40 and 42 to the intermediate image plane 38.

FIG. 4 schematically depicts the distribution of an exemplary number of RF comb beams in the intermediate image plane 38 (without loss of generality, the number of RF comb beams is selected to be 6 for illustration purposes (labeled as RF1, . . . , RF6), though other numbers can also be employed). As shown in FIG. 4, in the intermediate image plane 38, the RF comb beams 24 are spatially separated from one another along the horizontal direction. In other embodiments, two or more of the RF comb beams 24 may partially overlap. Thus, the combination of the lenses 26 and 30 transform the angularly separated RF comb beams into a set of spatially separated beams that span over a horizontal extent.

Referring again to FIG. 1, as discussed above, the beam splitter 44 receives the laser beam 22′ exiting the top-hat beam shaper 34 and reflects that beam to lens 46, which in turn focuses the beam on the intermediate image plane 48 in which the LO beam exhibits a top-hat beam profile. The beam splitter also receives the RF comb beams 24 from the intermediate image plane 38 and allows the passage of the RF comb beams there through. The lens 46 focuses the RF comb beams 24 onto the intermediate image plane 48 to be combined with the LO beam having a top-hat beam profile to generate a combined beam 49.

By way of illustration, FIG. 5 schematically depicts one exemplary profile of the combined beam 49 in a plane perpendicular to its propagation axis. The intensity profile of the combined beam is generated as a superposition of the intensity profile of the top-hat LO beam (shown schematically by the square) and those of the RF comb beams 24 (each shown schematically by one of the circles). As discussed in more detail below, this superposition of the LO beam and the RF comb beams provides, along a horizontal extent, a plurality of beat frequencies each corresponding to one spatial location along that horizontal extent. Upon illuminating a horizontal extent of a sample, the fluorescence radiation emitted from a location of the sample encodes, via amplitude modulation, the beat frequency associated with radiation illuminating that location.

Referring again to FIG. 1, a positive lens 50 (200-mm lens in this embodiment) and an objective lens 52, mounted in this embodiment on an adjustable post holder mount C, form a telescope for relaying the image at the intermediate plane 48 onto a sample flowing through a flow cell 54. In this embodiment, a mirror 56 reflects the combined beam 49 to the lens 50, and a dichroic mirror 58 reflects the combined light beam after its passage through the lens 50 toward the objective lens 52.

As shown schematically in FIG. 6, the combined beam 49 concurrently illuminates a plurality of spatial locations 60 of a sample 62 flowing through the flow cell 54. Thus, each location 60 is illuminated by the overlap of one of the RF comb beams with a portion of the top-hat shaped LO laser beam. At these spatial locations, the radiation will excite a fluorophore of interest in the sample, if present. More specifically, in this embodiment, the LO beam and the RF comb beams excite concurrently the fluorophore, e.g., via causing electronic transition thereof to an excited electronic state, at a plurality of sample locations 60.

In some embodiments, the sample can include a flowing fluid, in which a plurality of cells are entrained. In some cases, the cells can be labeled with one or more fluorescent markers (fluorophores). Some examples of fluorescent markers include, without limitation, fluorescent proteins (e.g., GFP, YFP, RFP), antibodies labeled with fluorophores (e.g., fluorescein isothiocyanate) (FITC), phycoerythrin (PE), allophycocyanin (APC)), nucleic acid stains (e.g., 4′,6-diamidino-2-phenylindole (DAPI), SYTO16, propidium iodide (PI)), cell membrane stains (e.g., FMI-43), and cell function dyes (e.g., Fluo-4, Indo-1). In other cases, endogenous fluorophores present in cells can be employed to elicit fluorescent radiation from the cells. As discussed in more detail below, such exogenous or endogenous fluorophores undergo electronic excitation in response to the illuminating radiation and emit fluorescent radiation (typically at a lower frequency than the excitation frequency), which is collected and analyzed.

By way of illustration and without being limited to any particular theory, FIG. 7 shows hypothetical energy levels corresponding to a ground electronic state A as well as two electronic excited electronic states B and C of a fluorophore. The fluorophore can be excited from its ground electronic state (A) to the excited electronic state (B) via absorption of radiation energy. The fluorophore can then relax into the lower excited state B, e.g., via a radiation-less transition mediated by vibrational modes of the fluorophore. The fluorophore can further relax from the lower electronic state C to the ground state, via an optical transition, thereby emitting fluorescence radiation at a frequency less than that of the excitation frequency. It should be understood that this hypothetical example is provided only for illustration purposes, and not to indicate the only mechanism by which fluorescence radiation can be emitted.

In many cases, the fluorophore can absorb electromagnetic radiation over a range of frequencies to be excited from the ground state to the excited electronic state. By way of illustration, FIG. 8 shows an absorption curve for the hypothetical fluorophore discussed in connection with FIG. 7. In one implementation of an embodiment according to the present teachings the LO frequency can be selected to coincide with the frequency corresponding to the peak absorption of a fluorophore of interest. The radiofrequency-shifted beams can have frequencies separated from the peak absorption by their respective beat frequencies. Typically, these frequency separations are small in comparison to the absorption bandwidth of the fluorophore so as to avoid any degradation of the excitation frequency. By way of example and only by way of illustration, the dashed lines A and B schematically depict the frequency of the LO beam and one of the RF comb beams (the figures is not drawn to scale for ease of description). The concurrent illumination of a spatial location of the sample by both the LO laser beam and one of the depicted RF comb beams results in fluorescence radiation exhibiting an amplitude modulation at a beat frequency corresponding to a difference between the LO and the RF comb beam frequencies.

Again by way of illustration and without being limited to any particular theory, the electric field applied to the fluorophore via its concurrent illumination by the LO beam and one of the RF comb beams can be mathematically defined as follows:

E _(com) =E _(RF) e ^(f(ω) ⁰ ^(+ω) ^(RF) ⁾ +E _(LO) e ^(j(ω) ⁰ ^(+ω) ^(LO) ⁾  Eq. (1)

wherein,

E_(com) denotes the electric field of the combined beam,

E_(RF) denotes the amplitude of the electric field associated with one of the RF comb beams,

E_(LO) denotes the amplitude of the electric field associated with the LO beam,

ω₀ denotes the frequency of the laser beam generated by the laser 12,

ω_(RF) denotes the frequency shift associated with the RF comb beam, and

ω_(LO) denotes the frequency shift associated with the LO beam.

The intensity of the fluorescence radiation emitted in response to the superposition of the electric fields of the LO and RF comb beams would exhibit a modulation at a beat frequency corresponding to (ω_(RF)−ω_(LO)). Hence, the fluorescence radiation emanating from each spatial location of the sample illuminated by superposition of the LO beam and one of the RF comb beams exhibits a modulation at a beat frequency corresponding to the difference between the radiofrequency shift associated with the LO beam and that associated with the RF comb beam illuminating that spatial location.

As the process of fluorescence emission requires a finite amount of time (typically 1-10 nanoseconds for common organic fluorophores), the emitted fluorescence will not exhibit a high modulation depth if the excitation beat frequency is too high. Thus, in many embodiments, the excitation beat frequencies are selected to be considerably less than 1/τ_(f), where τ_(f) is the characteristic fluorescence lifetime of the fluorophore. In some instances, the excitation beat frequencies may be less than 1/T_(f) by 1% or more, such as by 2% or more, such as by 3% or more, such as by 5% or more, such as by 10% or more, such as by 25% or more, such as by 50% or more, such as by 75% or more, such as by 90% or more, such as by 1.5-times or more, such as by 2-times or more, such as by 3-times or more and including 5-times or more. For example, the excitation beat frequencies may be less than 1/τ_(f) by 0.01 MHz or more, such as by 0.05 MHz or more, such as by 0.1 MHz or more, such as by 0.5 MHz or more, such as by 1 MHz or more, such as by 5 MHz or more, such as by 10 MHz or more, such as by 25 MHz or more, such as by 50 MHz or more, such as by 100 MHz or more, such as by 250 MHz or more, such as by 500 MHz or more and including 750 MHz or more. In some embodiments, the photodetector is configured to detect light (e.g., luminescence such as fluorescence) from the irradiated sample. In some embodiments, the photodetector may include one or more detectors, such as 2 or more detectors, such as 3 or more detectors, such as 4 or more detectors, such as 5 or more detectors, such as 6 or more detectors, such as 7 or more detectors and including 8 or more detectors. Any light detecting protocol may be employed, including but not limited to active-pixel sensors (APSs), quadrant photodiodes, image sensors, charge-coupled devices (CCDs), intensified charge-coupled devices (ICCDs), light emitting diodes, photon counters, bolometers, pyroelectric detectors, photoresistors, photovoltaic cells, photodiodes, photomultiplier tubes, phototransistors, quantum dot photoconductors or photodiodes and combination thereof, among other photodetectors. In some embodiments, the photodetectors of interest are configured to detect light that ranges from 350 nm to 1200 nm, such as from 450 nm to 1150 nm, such as from 500 nm to 1100 nm, such as from 550 nm to 1050 nm, such as from 500 nm to 1000 nm and including from 400 nm to 800 nm. In certain embodiments, the photodetector is configured to detect light at the emission maximum of luminescence, such as at 395 nm, 421 nm, 445 nm, 448 nm, 452 nm, 478 nm, 480 nm, 485 nm, 491 nm, 496 nm, 500 nm, 510 nm, 515 nm, 519 nm, 520 nm, 563 nm, 570 nm, 578 nm, 602 nm, 612 nm, 650 nm, 661 nm, 667 nm, 668 nm, 678 nm, 695 nm, 702 nm, 711 nm, 719 nm, 737 nm, 785 nm, 786 nm, or 805 nm.

In some embodiments, the fluorescence radiation emitted by the sample can be collected in a variety of different ways, e.g., along an optical path that is perpendicular to the propagation direction of the excitation beam. In other embodiments, the fluorescence radiation is detected in an epi-direction.

Referring again to FIG. 1, in this embodiment, the fluorescence radiation emitted by one or more fluorophores present in the illuminated sample passes through the objective lens 52 and is transmitted through the dichroic mirror 58 to reach a photodetector 64. More specifically, in this embodiment, a lens 65 focuses the fluorescent radiation transmitted through the dichroic mirror 58 onto a slit aperture 66. The fluorescent radiation that is transmitted through the slit passes through a fluorescence emission filter 68 to reach the photodetector 64. The slit aperture 66 (or an optical filter in other embodiments discussed below) disposed in front of the photodetector substantially allows the passage of the fluorescence radiation emitted from a particular plane of the sample while rejecting out-of-plane fluorescence emission. Further, the fluorescence emission filter 68, e.g., a passband filter, allows the passage of fluorescence radiation to the photodetector 64 while substantially blocking the passage of radiation at other frequencies.

The photodetector 64 has sufficient RF bandwidth to detect and transmit signals from the entire range of the beat frequencies. Some examples of suitable photodetectors include, without limitation, a photomultiplier tube, avalanche photodiode, PIN photodiode, and a hybrid photodetector, among others. By way of example, in some embodiments, a photomultiplier tube marketed by Hamamatsu Corporation can be employed (e.g., R3896, R10699, H11462). The photodetector generates a signal, e.g., an analog signal in this embodiment, in response to the detection of the received fluorescence radiation.

By way of another example and with reference to FIG. 9A, the fluorescence radiation emitted by the sample in response to concurrent illumination by the LO beam and the spatially separated RF comb beams passes through the objective lens 52 and the dichroic mirror 58 to be coupled via a lens 100 onto a multimode optical fiber 102, which extends from a proximal end 102 a to a distal end 102 b. More specifically, the proximal end 102 a of the optical fiber 102 is positioned in proximity of the focal plane of the lens 100 so as to receive the fluorescent radiation. An outcoupling lens 104, coupled to the distal end 102 b of the optical fiber, collimates the radiation exiting the fiber.

In many cases, the excitation radiation illuminating the sample excites multiple fluorophores (e.g., organic fluorophores) that can have broad enough radiation absorption spectra such that the excitation frequencies falls within the absorption spectra of multiple fluorophores in the sample. Each fluorophore would then emit fluorescence radiation at a different frequency. Without loss of generality and for purposes of illustration, in this embodiment, the detection system includes four photomultiplier tubes 106, 108, 110 and 112, each of which receives a portion of the collimated radiation corresponding to the fluorescence radiation emitted by one of four fluorophores excited by the excitation radiation in the illuminated sample. More specifically, a dichroic mirror 114 reflects the fluorescence radiation emitted by one of the fluorophores at a first frequency to the photomultiplier tube 106 while allowing fluorescence radiation at other frequencies to pass through. Another dichroic mirror 116 reflects the fluorescence radiation emitted by a different fluorophore at a different second frequency to the photomultiplier tube 108 while allowing the rest of the radiation containing fluorescence radiation emitted by yet another fluorophore at a third frequency to reach a third dichroic mirror 118, which reflects that fluorescence radiation to the photomultiplier tube 110. The dichroic mirror 118 allows the rest of the radiation including the fluorescence radiation emitted by a fourth fluorophore at a fourth radiation frequency to pass through to reach the photomultiplier tube 112.

A plurality of bandpass filters 120, 122, 124, and 126, each centered at one of the four fluorescence frequencies, are placed in front of the photomultiplier tubes 106, 108, 110, and 112, respectively. The signal detected by each of the photomultiplier tubes is analyzed in a manner discussed below to generate a fluorescence image at the respective fluorescence frequency. In some embodiments, rather than using multiple photodetectors, a single photodetector, e.g., a single photomultiplier tube can be used to detect fluorescence radiation, e.g., fluorescence frequency corresponding to emission from a single fluorophore.

In some embodiments, as the sample flows through the flow cell different horizontal rows of the sample are illuminated and fluorescence radiation associated with each horizontal row is detected by one or more photodetectors, such as the photomultipliers 106, 108, 110 and 112.

FIG. 9B schematically depicts a detection system similar to that discussed above in connection with FIG. 9A except that in this detection system, rather than using an optical fiber, the fluorescence radiation containing fluorescence emission from a plurality of fluorophores passing through the dichroic mirror 58 propagates in free space to reach the photomultiplier tubes 106, 108, and 112. More specifically, the lens 100 focuses the fluorescence radiation onto an aperture 126 disposed between the lenses 100 and 104, where the aperture can reject out-of-focus radiation. The lens 104 collimates the radiation passing through the aperture, where the collimated radiation is distributed among the photomultiplier tubes in a manner discussed above in connection with FIG. 9A.

In some embodiments, the system 10 can be configured to provide a darkfield image and a brightfield image of the sample (of the flow cell in absence of the sample) using the excitation radiation. By way of example, FIG. 9C schematically depicts an embodiment of the system 10 that includes two detection arms 200 and 202 for detecting, respectively, a darkfield image and a brightfield image of the sample.

More specifically, the detection arm 200 is positioned perpendicular to the propagation of the excitation radiation so as to receive a portion of the excitation radiation that is scattered by the sample flowing through the flow cell. The detection arm 200 includes two lenses 204 and 206 that collectively direct at least a portion of the excitation radiation scattered by the sample into a solid angle subtended by the lens 204 onto a photomultiplier tube 208. More specifically, the lens 204 collimates the received scattered radiation and the lens 206 focuses the collimated scattered radiation onto the photomultiplier tube 208. In this embodiment, an appropriate bandpass filter 210 is disposed in front of the photomultiplier tube 208 to allow the passage of radiation having the desired frequency to the photomultiplier tube 208 while blocking radiation at unwanted frequencies. The output of the photomultiplier tube 208 can be processed in a manner known in the art, e.g., by an analysis module such as that discussed below to generate a darkfield image.

The detection arm 202 in turn includes two lenses 212 and 214, where the lens 212 collimates the excitation radiation exiting the flow cell in a forward direction (substantially along the propagation direction of the excitation radiation entering the flow cell 54) and the lens 214 focuses the collimated radiation onto a photodetector 216. An appropriate filter 218, e.g., a bandpass filter, disposed in front of the photodetector allows transmission of the excitation frequencies to the photodetector 216 while substantially blocking other radiation frequencies. The output of the photodetector 216 can be processed in a manner known in the art to generate a brightfield image of the flow cell.

Thus, the detection arm 200 detects the excitation radiation that is scattered by the fluid flowing through the cell, and the detection arm 202 detects the excitation radiation that is transmitted through the flow cell. When no fluid is flowing through the flow cell, the signal detected by the photomultiplier tube 208 is low and the signal detected by the photodetector 216 is high as there is little scattering of the excitation radiation passing through the flow cell and hence a large percentage, and in some cases all, of the excitation radiation is transmitted through the flow cell. In contrast, the flow of a fluid sample through the flow cell can cause the signal generated by the photomultiplier tube 208 to increase due to scattering of a portion of the excitation radiation by the sample, and the signal generated by the photodetector 216 decreases as the level of the excitation radiation transmitted through the flow cell decreases.

By way of further example and with reference to FIG. 9D, in one embodiment of a system according to the present teachings, a detection arm 220 a positioned relative to the flow cell 54 in a direction substantially orthogonal to the propagation direction of the excitation radiation includes photodetectors for detecting both the fluorescence radiation emitted by a plurality of fluorophores in the sample as well as excitation radiation that is scattered by the sample. More specifically, the detection arm 220 includes lenses 222 and 224 that direct the fluorescence radiation as well as the scattered excitation radiation onto an aperture 226, which rejects unfocused radiation. A lens 228 collimates the radiation passing through the aperture. A dichroic mirror 230 reflects the portion of the radiation at the excitation frequencies onto a photomultiplier tube 232 for detection of a darkfield image while allowing fluorescence radiation to pass through. An appropriate filter 232 a, e.g., a bandpass filter, disposed in front of the photomultiplier tube 232 allows the passage of radiation at excitation frequencies to the photomultiplier tube 232 while blocking unwanted radiation frequencies. Another dichroic mirror 234 reflects fluorescence radiation emitted by a fluorophore at a first frequency onto a photomultiplier tube 236 while allowing the passage of fluorescence radiation emitted by other fluorophores at other frequencies. Another dichroic mirror 238 reflects fluorescence radiation emitted by another fluorophore at a second frequency onto a photomultiplier tube 240 while allowing the passage of fluorescence radiation emitted by yet another fluorophore at a third frequency, where it is detected by the photomultiplier tube 242. Similar to the previous embodiments, a plurality of filters 236 a, 240 a, and 242 a are disposed in front of the photomultiplier tubes 236, 240, and 242, respectively, to allow the transmission of radiation at desired frequencies while substantially blocking unwanted radiation frequencies.

With continued reference to FIG. 9D, this implementation of a system according to the present teachings further includes another detection arm 220 b for generating a brightfield image, e.g., in a manner discussed in connection with FIG. 9C. More specifically, the detection arm 202 includes two lenses 212 and 214 that focus the light onto a photodetector 216 for generating a brightfield image of the excitation radiation. A filter 218, e.g., a bandpass filter, is placed in front of the photodetector 216 to allow the passage of the excitation radiation to the detector while rejecting unwanted radiation frequencies.

Referring again to FIG. 1 as well as FIG. 10, in this embodiment, a transimpedance amplifier 70 can be coupled to the output of photodetector 64 (or each of the photodetectors discussed in connection with FIGS. 9A-9D) to amplify the signal generated by the photodetector. A data analysis unit 72 (herein also referred to as an analysis module or an analyzer) receives the amplified signal and analyzes the signal to generate a fluorescence image of the sample. The data analysis unit 72 can be implemented in hardware, firmware, and/or software. By way of example, a method for analyzing the detected fluorescence data can be stored in a read-only-memory (ROM) unit of the analysis module to be accessed under the control of a processor to analyze the received fluorescence signal.

As discussed in more detail below, the analysis method determines the frequency components of the time-varying photodetector's output and constructs a fluorescence image of the sample based on those frequency components. A variety of methods for determining the frequency content of the photodetector's output can be employed. Some examples of such suitable methods include, without limitation, Fourier transform, lock-in detection, filtering, I/Q demodulation, homodyne detection, and heterodyne detection.

By way of example, FIGS. 11A and 11B show exemplary analysis steps that can be performed by the analysis module 72 to generate a fluorescence image of the sample. In step (1), the analog amplified signal is digitized to generate digitized fluorescence data. In step (2), an appropriate portion (length) of the digitized data is selected for analysis. For example, the fluorescence data corresponding to an illuminated row of the sample (herein also referred to as a frame) can be chosen for analysis. Alternatively, a portion of a data frame can be selected for analysis.

In step (3), a Fourier transform of the selected data is performed. By way of example, in some embodiments, a Fast Fourier Transform (FFT) of the data is performed to determine frequency components of the data. In some such embodiments, the bins of the FFT can correspond to the frequencies chosen for data acquisition. For example, for a 256 MHz sampling rate, 256 samples can yield frequency bins that are separated from one another by 1 MHz, e.g., from DC to 128 MHz. The FFT analysis provides frequencies corresponding to the beat frequencies at which the emitted fluorescence emission exhibits amplitude modulation.

With continued reference to FIGS. 1A and 11B, in this embodiment, in step (4), a measure of the amplitude of each frequency component present in the FFT data is computed by obtaining the square root of the sum of squares of the real and imaginary components of that frequency component. As each frequency component corresponds to one of the beat frequencies employed to elicit the fluorescence radiation from a particular location of the sample, the measure of the amplitude of the frequency component can provide a pixel value for a location associated with that frequency component along a horizontal row of the sample. In this manner, pixel values for an image of a horizontal row of the sample can be determined. The above steps can be repeated for fluorescence data obtained for each horizontal row of the sample as the sample flows through the flow cell in a vertical direction. The pixels values can be used to construct a fluorescence image (step 5).

As noted above, the analysis module 72 can be implemented in hardware, firmware and/or software using techniques known in the art and in accordance with the present teachings. By way of example, FIG. 12 schematically depicts an exemplary implementation of analyzer 72, which includes an analog-to-digital converter 74 for receiving the amplified fluorescence signal from the amplifier 70 and digitizing that signal to generate digitized fluorescence data. The analysis module further includes a central processing unit (CPU) 76 for controlling the operation of the analysis module, including performing calculations and logic operations. The analysis module also includes ROM (read only memory) 78, RAM (random access memory) 80 and permanent memory 82. A communications bus 84 facilitates communication among various components of the analysis module, including communications between the CPU 76 and other components. The memory modules can be used to store instructions for analyzing the fluorescence data and the analysis results. By way of example, in some embodiments, instructions for data analysis, e.g., instructions for performing the above steps discussed in connection with FIGS. 11A and 11B, can be stored in the ROM 78. The CPU can employ instructions stored in ROM 78 to operate on digitized fluorescence data stored in RAM 80 to generate a fluorescence image of the sample (e.g., a one-dimensional or a two-dimensional image). The CPU can effect the storage of the fluorescence image in permanent memory 82, e.g., in a database. As shown schematically in FIG. 12, the analysis module can optionally include a graphics processing unit (GPU) 76′ for performing calculations of pixel intensities and other quantities from the received data (e.g., fluorescence data).

In some embodiments, the frequency demodulation of the output signal generated by the photodetector can be achieved using lock-in detection techniques. By way of example, with reference to FIGS. 13A and 13B, in one such embodiment, the amplified fluorescence signal is digitized (step 1) and several copies of the digitized fluorescence signal are generated (step 2), where the number (N) of the digitized copies corresponds to the number of frequencies associated with the RF comb beams. Each digitized copy of the signal is multiplied with sine and cosine waves having a frequency corresponding to a beat frequency equal to a difference between the frequencies of one of the RF comb beams and the LO beam to generate a plurality of intermediate signals (step 2). Each intermediate signal is passed through a low-pass filter (step 3), which has a bandwidth equal to one half of the frequency spacing between the RF comb frequencies.

For each beat frequency corresponding to one of the RF comb frequencies (in other words, for each frequency corresponding to a spatial location of the illuminated sample), square root of the sum of the squares of the two filtered intermediate signals corresponding to that frequency is obtained as a measure of the amplitude of an image pixel corresponding to the sample location illuminated by the LO beam and the RF comb beam having that frequency (step 4). In some embodiments, multiple fluorescence data signals corresponding to the same beat frequency (i.e., corresponding to the same sample location) can be processed in a manner discussed above and the pixel values can be averaged so as to obtain an average pixel value.

The above steps can be repeated for fluorescence data obtained for each horizontal row of the sample as the sample flows through the flow cell in a vertical direction. The pixels values can be used to construct a fluorescence image (step 5).

The above lock-in detection method can be implemented in software, firmware and/or hardware. By way of example, in one embodiment the above lock-in detection method can be implemented using a field programmable gate array (FPGA), particularly if more than 6 frequencies are used. In some embodiments, a multi-frequency lock-in amplifier, such as HF2L-MF multi-frequency amplifier marketed by Zurich Instruments of Zurich, Switzerland can be employed.

By way of further examples, in some embodiments the frequency demodulation of the detected fluorescence signal can be achieved by employing a bandpass filter-based image demodulation technique. By reference to FIGS. 14A and 14B, in one embodiment of such a frequency demodulation method, the fluorescence signal provided by the photodetector 64 and the amplifier 70 is digitized (step 1) and several copies of the digitized signal are generated (step 2), where the number (N) of the digitized copies corresponds to the number of frequencies associated with the RF comb beams. Each copy of the digitized fluorescence signal is filtered by passing that signal through a bandpass filter centered at a beat frequency associated with one of the RF comb beams (i.e., a beat frequency associated with a particular location of the sample) (step 3). More specifically, each bandpass filter is centered at one of N beat frequencies and has a bandwidth that is equal to half of the frequency spacing between adjacent beat frequencies.

An envelope detector at each beat frequency is employed to estimate, for each horizontal line, the amplitude of each pixel corresponding to that frequency (step 4). In some cases, a plurality of pixel values corresponding to a pixel, obtained by processing multiple fluorescent signals corresponding to a sample location associated with that pixel, is averaged to obtain an average pixel value. The above steps can be repeated for fluorescence data obtained for each horizontal row of the sample as the sample flows through the flow cell in a vertical direction. The pixels values can be used to construct a one-dimensional or a two-dimensional fluorescence image of the sample (step 5).

The analysis module can also be configured to receive and process the brightfield and darkfield image data. For example, with reference to FIG. 9C and FIG. 10, the analysis module 72 can be further configured to receive the darkfield and brightfield image data from photodetectors 208 and 218 to generate darkfield and brightfield images. For example, with reference to FIG. 12, the instructions for generating the darkfield and brightfield images, e.g., in a manner known in the art, can be stored in permanent memory 82. The processor 76 can employ these instructions to process the received darkfield and brightfield image data to generate the images. The analysis module can be also configured to generate composite images by overlaying, e.g., a fluorescence image and one or both of the brightfield and darkfield images.

The fluorescence images as well as the brightfield and darkfield images generated by a system according to the present teachings, such as the above system 10, can be used for a variety of different ways. For example, the fluorescence image can be integrated to produce a value comparable to the data produced by a conventional flow cytometer. The fluorescence image can also be analyzed to determine the location of fluorescent probe giving rise to that image (e.g., it can be determined whether the probe is the nucleus, cytoplasm, localized to organelles, or on the outside of the cell membrane). Further, in some applications, multiple fluorescent images obtained by detecting different fluorescent bands, all of which taken from the same cell, can be used to determine the degree of co-localization of multiple fluorescent probes within a cell. Additionally, the analysis of cell morphology, cell signaling, internalization, cell-cell interaction, cell death, cell cycle, and spot counting (e.g., FISH), among others, are possible using multi-color fluorescence, brightfield, and darkfield images.

As noted above, the system 10 can be operated in at least three different modes. In one mode discussed above, an LO beam and a plurality of RF comb beams concurrently illuminate a portion of the sample (e.g., locations disposed along a horizontal extent), and the fluorescence radiation emitted from the illuminated locations is detected and analyzed in order to construct a fluorescence image of the sample. In another operational mode, rather than applying a plurality of RF drive signals concurrently to the AOD, a frequency ramp containing the drive signals is applied to the AOD such that the frequency of the laser beam is changed over time from a start frequency (f₁) to an end frequency (f₂). For each drive frequency in the frequency ramp, the frequency of the laser beam is shifted by that drive frequency and the sample is illuminated by the frequency-shifted laser beam to elicit fluorescence radiation from the sample. In other words, in this mode, the system is operated to obtain fluorescence radiation from the sample by illuminating the sample successively over a temporal interval with a plurality of frequencies, which are shifted from the central laser frequency. The frequency shift generated by the AOD is accompanied by an angular deflection such that using the same optical path, the beam is scanned across the sample at a high speed.

More specifically, in this operational mode, the RF frequency synthesizer 10 is employed to ramp a drive signal applied to the AOD 18 from a start frequency (f₁) to an end frequency (f₂). By way of example, the frequency range over which the drive signal is ramped can be from about 50 MHz to about 250 MHz. In some embodiments, the drive signal is ramped from about 100 MHz to about 150 MHz. In this embodiment, the drive frequency is changed over time continuously, e.g., to achieve a high speed. In other embodiments, the drive frequency can be changed in discrete steps from a start frequency (f₁) to an end frequency (f₁).

The drive frequencies are chosen such that the frequency-shifted beam would miss the mirror 28 and propagate along an optical path defined by lens 26, lens 30, mirrors 40/42, a beam splitter 44, lens 46, mirror 56, lens 50, mirror 58 and the objective lens 52 to illuminate a portion of the sample flowing through the sample holder. The ramp rate is preferably fast enough so as to ameliorate and preferably prevent, any blur in the vertical direction of a fluorescence image to be generated based on the emitted fluorescence radiation as the sample flows across the beam. This can be achieved, for example, by matching the ramp rate with the sample's flow speed. The laser spot size at the sample can be used to estimate appropriate rates. By way of example, for a laser spot size of 1 micrometer, the scan time across 1 line should be 10 microseconds or less for a sample flow speed of 0.1 meters per second to avoid image blur.

The fluorescence radiation emitted from the sample in response to illumination by the excitation radiation is collected and detected in a manner discussed above. Specifically, with reference to FIG. 10, the fluorescence radiation is detected by photodetector 64. The detected fluorescence is amplified by the amplifier 70 and the amplified signal is analyzed by the analysis module 72 to reconstruct a fluorescence image of the sample. The reconstruction of the image is performed by assigning a horizontal pixel location to a specific time within the scan period from the start frequency (f₁) to the end frequency (f₂). As opposed to analyzing the amplitude of a frequency component to obtain pixel values as in the above operational mode, the demodulation approach used in this operational mode only uses the time domain values of the detected fluorescence signal to assign values to the pixels of the image. The process can be repeated as the sample flows in a vertical direction so as to obtain a two-dimensional fluorescence image of the sample.

The fluorescence radiation, if any, emitted by the sample is collected by photodetector 64. Referring to FIG. 10, the detected fluorescence radiation is amplified by the amplifier 70. The analysis module 72 receives the amplified signal. In this operational mode, the analysis module analyzes the fluorescence signal to determine the fluorescence content of the sample, e.g., a cell/particle. Since there is only one beam exciting the sample in this operational mode, no beat frequencies are generated in response to exciting the sample. Hence, there is no image information in the frequency domain of the fluorescence signal. Rather, the detected fluorescence signal has image information encoded in the time domain. In this operational mode, an image can be digitally reconstructed using the time values of the detected fluorescence signal as the horizontal pixel coordinate, and the digitized voltage values of the fluorescence signal as the pixel values (brightness). Each scan of the drive frequencies applied to the AOD produces one horizontal line (row) of the image. The image reconstruction is achieved via consecutive scans as the sample flows through the illumination area (point).

In yet another operational mode, the system 10 can be operated to illuminate a plurality of locations of a sample concurrently by a single excitation frequency, which can be generated, e.g., by shifting the central frequency of a laser beam by a radiofrequency. More specifically, referring again to FIG. 1, in such an operational mode a single drive radio frequency can be applied to the AOD 18 to generate a laser beam having a frequency that is shifted relative to the laser beam entering the AOD 18. Further, the frequency-shifted laser beam exhibits an angular shift relative to the laser beam entering the AOD such that the radiofrequency laser beam is intercepted and reflected by the mirror 28 towards the top-hat beam shaper 34 via lens 32 and mirrors 33 and 35. The beam exiting the top-hat beam shaper is reflected by the beam splitter 44 and is focused by the lens 46 onto the intermediate image plane 48. In this plane, as shown schematically in FIG. 15A, the laser beam 1000 shows a stretched profile along the horizontal direction.

The horizontally-stretched laser beam is reflected by the mirror 56 to the positive lens 50. After passage through the lens 50, the laser beam is reflected by the mirror 58 to the objective lens 52. As discussed above, the positive lens 50 and the objective lens 52 form a telescope for relaying the top-hat profiled laser beam from the intermediate image plane 48 onto a sample flowing through the flow cell 54.

The horizontally-stretched laser beam illuminates a horizontal extent of the sample to excite a fluorophore of interest, if present in the sample, along that horizontal extent. Thus, in this operational mode, unlike the first operational mode in which a plurality of horizontal locations of the sample is illuminated at different excitation frequencies, a plurality of horizontal locations of the sample is illuminated at the same excitation frequency. This operational mode does not enable a user to obtain an image of cells or particles that flow by. However, in this operational mode, a higher optical power can typically be applied to the sample than in the other two operational modes, which can be useful for obtaining a higher signal-to-noise ratio data if images are not required. This operational mode is accessible by merely altering the electronic signal driving the acousto-optic deflector, without a need to make any mechanical changes to the system.

Thus, the system 10 can be operated in three distinct operational mode to elicit fluorescence radiation from a sample.

In some embodiments, fluorescence lifetime measurements can be performed at each spatial position on the sample, e.g., by comparing the phase of the beats of each of the radiofrequency-shifted and local oscillator beams with the phase of a respective radiofrequency component in the detected fluorescence signal. By way of example, FIG. 15B shows a system 10′, a modified version of the system 10 discussed above, that allows for such fluorescence lifetime measurements (certain components shown in FIG. 1 are not depicted in this figure for brevity). Specifically, a portion the RF comb beams incident on the beam splitter 44 is reflected by the beam splitter onto a convergent lens 400 (by way of illustration in this embodiment the lens 400 has a focal length of 200 mm, though other focal lengths can also be used). The lens 400 focuses that portion of the RF comb beams onto a photodiode 402, which detects the excitation beam. The output of the photodiode 402 can be received by the analysis module 72 (See, FIG. 10). The analysis module can provide frequency de-multiplexing of the excitation beam, e.g., using one of the de-modulation techniques discussed above and determine the phase of each radio frequency component in the excitation beam. This can provide, for each radiofrequency component in the detected fluorescence signal, a reference phase with which the phase of that radiofrequency component can be compared. For example, the real and imaginary components of an FFT of the excitation signal or the I and Q components of lock-in type demodulation can be employed. Alternatively, the output of the detector detecting the brightfield image of the sample/flow cell can be used to obtain reference phases with which the phases of the fluorescence beat frequencies can be compared.

More specifically, the analysis module 72 can provide frequency de-multiplexing of the detected fluorescence signal, e.g., in a manner discussed above. As will be appreciated by one skilled in the art, for each beat frequency in the fluorescence signal, the phase of the radiofrequency component can be compared with the respective reference phase of the excitation beam to obtain spatially-resolved fluorescence lifetime measurements and a fluorescence lifetime image.

In certain embodiments, the subject systems include flow cytometry systems employing the optical configuration described above for detecting light emitted by a sample in a flow stream. In certain embodiments, the subject systems are flow cytometry systems which include one or more components of the flow cytometers described in U.S. Pat. Nos. 3,960,449; 4,347,935; 4,667,830; 4,704,891; 4,770,992; 5,030,002, 5,040,890; 5,047,321; 5,245,318; 5,317,162; 5,464,581; 5,483,469; 5,602,039; 5,620,842; 5,627,040; 5,643,796; 5,700,692; 6,372,506; 6,809,804; 6,813,017; 6,821,740; 7,129,505; 7,201,875; 7,544,326; 8,140,300; 8,233,146; 8,753,573; 8,975,595; 9,092,034; 9,095,494; and 9,097,640, the disclosures of which are herein incorporated by reference in their entirety.

As discussed above, in some embodiments the subject systems are configured for imaging particles (e.g., cells) in a sample flowing as a flow stream, such as in the flow stream of a flow cytometer. The flow rate of particles in the flow stream may be 0.00001 m/s or more, such as 0.00005 m/s or more, such as 0.0001 m/s or more, such as 0.0005 m/s or more, such as 0.001 m/s or more, such as 0.005 m/s or more, such as 0.01 m/s or more, such as 0.05 m/s or more, such as 0.1 m/s or more, such as 0.5 m/s or more, such as 1 m/s of more, such as 2 m/s or more, such as 3 m/s or more, such as 4 m/s or more, such as 5 m/s or more, such as 6 m/s or 0 μL/min or more, such as 7 m/s or more, such as 8 m/s or more, such as 9 m/s or more, such as 10 m/s or more, such as 15 m/s or more and including 25 m/s or more. For example, depending on the size of the flow stream (e.g., the flow nozzle orifice), the flow stream may have a flow rate in the subject system of 0.001 μL/min or more, such as 0.005 μL/min or more, such as 0.01 μL/min or more, such as 0.05 μL/min or more, such as 0.1 μL/min or more, such as 0.5 μL/min or more, such as 1 L/min or more, such as 5 μL/min or more, such as 10 μL/min or more, such as 25 μL/min or more, such as 50 μL/min or more, such as 100 μL/min or more, such as 250 μL/min or more and including 500 μL/min or more.

As discussed above, a number of techniques can be employed to reconstruct an image (e.g., a fluorescent image) from the temporal data (signal), such as fluorescence data, obtained by interrogating a sample. In some embodiments, a forward model is employed that provides an expected signal (e.g., a fluorescent signal) based on an underlying image to analyze a measured signal so as to arrive at an underlying image that is most likely to have generated that signal. In some embodiments, the forward model can be inverted to produce a reverse model for operating on a measured signal to obtain an image. For example, the forward model may treat the underlying image as the magnitude of a spectrogram. In such a case, a signal giving rise to the image can be obtained via the application of an inverse Fourier transform to the image. The reverse model would then entail the application of the Fourier transform to a measured signal to arrive at the image.

In some embodiments, a model indicative of how a cytometric system according to the present teachings converts an underlying “true image” of a sample illuminated by a plurality of optical beams separated from one another by one or more RF frequencies into a temporal signal to be measured is constructed. By inverting this model and incorporating known or measured parameters of the system, the measured signal can be converted into an estimate that more closely matches the underlying true image. By way of further illustration, FIG. 20 schematically shows how such a model can be constructed. The generation of a “true image” of a sample, represented as two-dimensional intensity map ((x,y)), and its conversion to a measured signal (y(t)) are influenced by a plurality of properties of components of the cytometric system, such as an illumination system, an optical collection system, and electronic system used in the detection arm. By way of example, the illumination system can include, among other elements, a laser beam, an acousto-optic deflector receiving the laser beam, and an RF generator for applying RF signals to the deflector so as to generate a plurality of optical beams separated in frequency by one or more RF frequencies. Knowledge about the parameters associated with these systems (indicated by ovals) improves the ability to estimate the image of the sample. For example, in some embodiments, a response of the electronic component can be measured from the portions of a Fourier spectrum of a measured output response of the electronic component that do not contain the image signal. A model for the response rolloff can be assumed, and the model can be fitted to the measured response.

The illumination spots at the sample can be generated by optical interference of two beams with slightly different frequencies. A difference in the path length of the beams can cause a phase shift in the beat frequency at the sample. In many embodiments, even minute path-length variations due to mechanical vibration of the system (e.g., caused by cooling fans) can affect the phase of the beams at the sample. In order to deploy lock-in detection, these phase changes must be accounted for. In some embodiments, the phase shift before and after every event can be measured using the phase content of the Brightfield signal, which has typically a high signal-to-noise ratio (SNR) and otherwise should not change phase. The resulting phase shift can be modeled as a rotation of the Fourier components of the signal, which is divided out in frequency domain.

In some embodiments, the shot noise associated with the electronic system can manifest itself in an image as rows of white Gaussian noise, proportional to the amount of signal that is present in that row. This is unlike most noise models in traditional imaging, which assume either independent Gaussian noise or pixel-wise Poisson noise (noise in each pixel is proportional to the intensity of that pixel). In some embodiments, the image quality can be improved by finding the maximum likelihood of an underlying image, given that the image is corrupted by noise with this characteristic. One technique applies the fact that naturally-occurring images are dissimilar from white noise where pixels have no correlation. Such a technique can assume that the true image contains many regions of relatively flat intensity. This represents the estimation as an optimization problem; one needs to find an estimate for an image that is as close to the measured signal as possible, but minimizes that amount of variation within the estimate. In some embodiments, this can be achieved by the following cost function:

∥G−y∥+λ(r)*TV(G),

where ∥G−y∥ represents the distance between an estimate of the image (G) and the measured image plus the total variation of the guess G (weighted by a penalty term λ, which is row-dependent). This cost function can be minimized to obtain the best-fit image of the sample. Any optimization approach can be used to perform this minimization (including particle swarm optimization, genetic algorithms, or gradient descent).

As noted above, in some cases, a forward model can also incorporate models of various noise contributions to the signal, such as a shot noise model and models of the noise contributions from photomultiplier tubes and/or electronic amplifiers, such as multiplicative noise, thermal noise, harmonic distortion, and nonlinear distortions.

In some embodiments, statistical techniques can be employed to fit model parameters to measured data. In some such embodiments, the forward model cannot be directly inverted. In some cases, such statistical techniques operate as maximum likelihood estimators to generate model parameters that are most likely to give rise to the measured data. Further, in some embodiments, an image reconstructed using a reverse model, e.g., FFT or lock-in-based processing discussed above, can be used as an initial (seed) image for such statistical techniques to further enhance the signal-to-noise ratio and/or the resolution of the image.

By way of example, with reference to the flow chart of FIG. 19A, in one exemplary method for performing flow cytometry according to the present teachings, a sample is illuminated with a laser radiation, and at least a portion of a radiation emanating from the sample in response to the illumination is detected to generate a temporal signal corresponding to the detected radiation. A statistical analysis of the signal based on a forward model is performed so as to reconstruct an image of the sample. The image can be any of a fluorescence, darkfield and brightfield image of the sample.

By way of further illustration, some examples of such statistical techniques are provided below.

One example of such a statistical technique is a least squares optimization, which can model a system/process as the sum of a plurality of linear components with normally-distributed error. By way of example, with reference to FIG. 19B, a cytometry signal (e.g., a fluorescence, a brightfield and/or a darkfield) signal can be modeled by breaking up the signal into a plurality of short temporal segments (e.g., segments of about 1-100 microseconds in duration) (step 1). In some embodiments, each segment can be modeled as having one sinusoidal, and one cosinusoidal term for each image pixel together with zero, first and second order terms, resulting in (2×N+3)×M parameters to fit an N×M pixel image. Further, each segment can also be modeled to include noise, e.g., a normally-distributed noise. A least squares regression analysis can then be employed (step 2) to obtain estimated values for the parameters of the model by minimizing the sum of the squared residuals corresponding to the differences between temporal segments predicted by the model and the respective temporal segments associated with a measured cytometry signal. A least squares optimization method for use in the reconstruction of cytometric images can be fast and can be implemented, e.g., using matrix operations.

By way of further example, with reference to FIG. 19C, a sample can be illuminated with laser radiation (step 1), and a radiation emanating from the sample in response to its illumination by laser radiation (e.g., fluorescent radiation in this embodiment) can be detected to generate a fluorescent signal corresponding to the detected radiation (step 2). For example, the above system can be employed to acquire radio-frequency tagged fluorescence data. A least squares analysis can be employed to obtain best estimates of the parameters associated with a model of a pixelated image of the sample (e.g., a fluorescent image of the sample in this embodiment) by minimizing the sum of squared residuals corresponding to a difference between a fluorescent signal inferred from the model and the measured fluorescent signal (step 3).

In some embodiments, a gradient descent optimization method can be employed for the reconstruction of a cytometric image, e.g., a fluorescence, a brightfield, and/or a darkfield image. This method allows employing a non-linear model, thereby reducing the number of free parameters, typically at the expense of computation time. With fewer free parameters, the model variance can decrease, thereby improving the signal-to-noise ratio (SNR) of the image. The gradient descent is an iterative optimization method that can begin with an initial estimate for an image (e.g., a fluorescent image). More specifically, with reference to the flow chart of FIG. 19D, in such an embodiment, a sample can be illuminated with a laser radiation (step 1), and radiation emanating from the sample in response to illumination, e.g., fluorescent radiation, can be detected to generate temporal data (step 2). The temporal data can be processed to generate an initial estimate of an image of the sample. For example, in some embodiments, such an estimate can be obtained via application of FFT or the above least squares method to the temporal data, e.g., fluorescent data, obtained from a sample. The initial estimate of the image is iteratively improved to obtain a final image of the sample. At each iteration, an error function indicative of a distance between the expected signal and the measured signal and the associated error gradient are computed, and the image is stepped down the error gradient. The iterative process is repeated until the error is minimized, thereby producing the best-fit image (step 3). A step-size for stepping the image down the error gradient can be selected, e.g., based on a tradeoff between computation time and accuracy.

In some cases, the gradient descent optimization method may not reach the best global image, as the optimization process can get trapped in a local minimum of the parameter space. Hence, in some embodiments, the particle swarm optimization can be employed for the reconstruction of a cytometric image. Similar to the gradient descent optimization method, the particle swarm optimization can begin with an estimate of the image (e.g., an estimate of a fluorescent image obtained via application of FFT or least squares method to detected fluorescent data). The particle swarm optimization then employs a plurality (“swarm”) of models, each of which is referred to as a particle, that randomly sample the parameter space in a way that is biased toward their negative error gradients. By controlling the degree of random sampling, the swarm can escape local minima at the expense of slower convergence.

In some embodiments, a genetic algorithm optimization is used in the reconstruction of an image. In such a method, a population of models with randomly varying parameters is employed. Each model “fitness” is evaluated, e.g., based on the degree of error between the predicted and measured image data. The models having a “fitness” greater than a threshold are then selected and their parameters are randomly combined to produce a new generation of models. These offsprings undergo the same process until the most fit models remain. In particular, the pixels in the image are the parameters used in the genetic algorithm. A forward model of the system converts this set of parameters into an expected temporal signal, then the difference between the expected signal and measured signal is used to evaluate the fitness of the model. Images that produce time signals that are very different from the measured signal are considered to be less fit.

In some embodiments, a priori information about an image signal (e.g., a fluorescent, brightfield or darkfield signal) can be used together with Bayesian spectral estimation to obtain a high resolution image. By way of example, in some embodiments, it may be known that the image signal is composed of a number of sinusoids of unknown frequencies and amplitudes. In some such embodiments, a Bayesian spectral estimation method can be used to estimate the parameters of those sinusoids at a greater degree of accuracy and precision than that obtainable using a conventional power spectrum approach. This can in turn result in a greater frequency resolution than is conventionally possible, thus allowing super-resolution imaging. In other words, in such embodiments, the time-domain signal can be treated as multiple independent measurements with a limited number of parameters and the maximum likelihood estimate for the parameters can be obtained.

The above methods for image reconstruction can be implemented in hardware, firmware and/or software. By way of example the above data analysis module 72 (See, e.g., FIG. 10) can be configured to perform the above image reconstruction methods using statistical analysis techniques. By way of example, a program containing the requisite steps for performing the above methods can be stored in memory unit, e.g., a ROM, of the analysis module. The processor of the module can then access the program to apply the steps of the image reconstruction method to the temporal data, e.g., fluorescence data, received from a sample under study.

The following examples are provided solely for further elucidation of various aspects of the present teachings and are not intended to illustrate necessarily the optimal ways of implementing the teachings of the invention or the optimal results that can be obtained.

Example 1

A system similar to that described above in connection with FIG. 1 with a detection system similar to that described above in connection with FIG. 9A was employed to measure fluorescence radiation from polystyrene beads stained with 8 discrete levels of fluorescence dyes, which are marketed by Spherotech Inc. of Lake Forest, Ill. under tradename RCP-30-5A. The system was also used to generate brightfield and darkfield images in a manner discussed above.

FIG. 16A is a scatter plot of darkfield intensity versus brightfield intensity. The rectangular section of the plot was used as a gate to generate the data depicted in FIGS. 16B, 16C, and 16D, which contains about 32% of all events measured (50,000 total events were detected). FIG. 16B shows a scatter plot of the red fluorescence (PI) v. green fluorescence (FITC) emitted by each particle. This plot clearly shows 8 populations with varying levels of brightness. FIGS. 16 C and 16D are histograms of the same data.

Example 2

FIRE, brightfield, and darkfield images of fixed peripheral blood leukocytes stained with CD45-FITC and propidium iodide were obtained using a system similar to that described above in connection with FIG. 1 with a detection system similar to that discussed above in connection with FIG. 9A. The sample also contained a fraction of live HeLa cells, stained with Calcein-AM. The cells were flowing through the flow cell at a rate of 0.5 meters/second during data acquisition.

The images shown in FIG. 17A are from top to bottom: overlay of bright-field, CD45-FITC, and propidium iodide fluorescence channels, bright-field, dark-field, CD45-FITC, and PI channel fluorescence. No compensation has been applied, and all images are auto-scaled for viewing. Cells numbered 2, 3, 5, 8, 9, 12, 17, 20, and 21 are HeLa cells (B population), and the others are leukocytes (A population).

FIG. 17B is a scatter plot in which population A represents leukocytes and population B represents HeLa cells.

Example 3

FIRE, brightfield, and darkfield images of fixed peripheral blood leukocytes stained with CD45-FITC and propidium iodide were obtained using a system similar to that described above in connection with FIG. 1 with a detection system similar to that discussed above in connection with FIG. 9A. The sample was spiked with a small fraction of fixed MCF-7 cells, stained with anti-EpCAM-FITC and propidium iodide (PI). The cells were flowing through a flow cell at a rate of 0.5 meters/second during data acquisition.

The images shown in FIG. 18A are from top to bottom: an overlay of brightfield, FITC, and PI channel fluorescence, brightfield, darkfield, FITC, and PI fluorescence. In the leukocyte population, green fluorescence is an artifact of fluorescence spillover from the PI stain. All images were auto-scaled in brightness for viewing, and thus, leukocytes appear to exhibit FITC fluorescence, yet this is a small fluorescence spillover signal from the PI. Cells numbered as 1, 2, 4, 5, 10, 13, 15, and 16 are MCF-7 cells.

FIG. 18B is a scatter plot in which population A represents leukocytes, and population B represents MCF-7 cells.

Example 4

FIG. 21A depicts a high signal-to-noise (SNR) FIRE measurement of light extinction and scattering by an elongated Euglena (algae) cell, such that the presence of the cell causes a reduction in signal. FIG. 21B shows an image of the cell obtained by extracting the Fourier components of the signal shown in FIG. 21A. This is an acceptable image of the cell. However, this image can be improved by incorporating information about the FIRE excitation signal, electronic response, and phase response of the system, in a manner discussed above, to produce the image depicted in FIG. 21C.

Example 5

FIG. 22A depicts a low signal-to-noise FIRE measurement of the lipid content of the Euglena cell of Example 4 via fluorescence. Although there is a clear pulse created by the fluorescent target, a large amount of noise corrupts the signal. FIG. 22B shows the result of extracting the Fourier coefficients of the signal; the cell is unrecognizable against the noise. Incorporating information about the frequency response of the collection electronics, the underlying FIRE signal driving the system, and phase response of the system, produces an improved but noisy image shown in FIG. 22C. A more sophisticated model of the underlying signal and the impact of photonic shot noise, in a manner discussed above, produces the image depicted in FIG. 22D.

Those having ordinary skill in the art will appreciate that various changes can be made without departing from the scope of the present teachings. In particular, various features, structures, or characteristics of embodiments discussed above can be combined in a suitable manner. For example, the detection systems discussed in connection with one embodiment may be used in another embodiment. 

1.-27. (canceled)
 28. A method for performing flow cytometry, comprising: illuminating a sample with a laser radiation, deploying a detector to detect at least a portion of a radiation emanating from the sample in response to said illumination and to generate a temporal signal corresponding to said detected radiation, and utilizing a computer processor to perform a statistical analysis of said signal based on a forward model so as to reconstruct an image of said sample.
 29. The method of claim 28, wherein said image is any of a fluorescence, a darkfield, and a brightfield image.
 30. The method of claim 29, wherein said laser radiation includes at least two optical frequencies shifted from one another by a radiofrequency to elicit fluorescence radiation from the sample, wherein said temporal signal comprises one or more beat frequencies associated with the radiofrequency-separated optical frequencies.
 31. The method of claim 30, further comprising processing said temporal signal to generate a fluorescence image and using said fluorescence image as a seed image for performing said statistical analysis.
 32. The method of claim 29, wherein said statistical analysis employs a least squares method to obtain said reconstructed image by minimizing a sum of squared residuals corresponding to a difference between said detected temporal signal and a respective temporal signal inferred from said forward model.
 33. The method of claim 32, wherein said temporal signal is a fluorescence signal.
 34. The method of claim 33, wherein said temporal signal is a scattering signal.
 35. The method of claim 31, further comprising modeling said detected temporal signal as a plurality of temporal segments each having one sinusoidal and one cosinusoidal term.
 36. The method of claim 35, wherein said statistical analysis employs a least squares regression analysis so as to obtain values for parameters of said model of the temporal signal by minimizing a sum of squared residuals corresponding to differences between said modeled and the respective measured temporal segments.
 37. The method of claim 29, wherein said forward model comprises a non-linear model.
 38. The method of claim 37, wherein said statistical analysis comprises a gradient descent optimization method.
 39. The method of claim 38, wherein said gradient descent optimization method calculates an error gradient indicative of a distance between an expected temporal signal based on said forward model and the measured temporal signal and iteratively computes an updated image by stepping a previous image down the error gradient.
 40. The method of claim 39, wherein said gradient descent optimization method starts said iterative computation with an initial estimated image computed based on the measured temporal signal.
 41. The method of claim 40, further comprising using said processor to compute said initial estimated image via application of a Fast Fourier Transform (FFT) to said measured temporal signal.
 42. The method of claim 29, wherein said statistical analysis employs a priori information about said measured temporal signal in combination with Bayesian spectral estimation to reconstruct said image of the sample.
 43. The method of claim 42, wherein said a priori information indicates that said temporal signal is composed of a number of sinusoids of unknown frequencies and amplitudes.
 44. The method of claim 43, wherein said Bayesian spectral estimation provides estimates of said unknown frequencies and amplitudes of the sinusoids.
 45. The method of claim 29, wherein said statistical analysis employs a particle swarm optimization method.
 46. The method of claim 29, wherein said statistical analysis employs a genetic algorithm.
 47. The method of claim 31, wherein said radiofrequency is in a range of about 10 MHz to about 250 MHz.
 48. The method of claim 29, wherein said sample comprises any of a cell, a micro-vesicle, a cellular fragment, a liposome, a bead, and a small organism.
 49. The method of claim 29, wherein said laser radiation has a frequency in a range of about 300 THz to about 1000 THz. 